Optical specimen analysis system and method

ABSTRACT

A method and system for automatic analysis of a testing substrate for an analyte in a liquid sample. The sample is applied to a testing substrate having an immobilized thereon, in a limited region of the testing substrate, a receptor capable of binding to the analyte. A labeled reagent, capable of binding to the analyte, is added to the testing substrate. If the analyte is present, a color is generated at the area of the testing substrate where the receptor is immobilized. The testing substrate is then illuminated and, using electronic equipment a digital image of the testing substrate is acquired and automatically scanned to locate an area of the testing substrate having the highest color density and generating a first measurement of color density. Next, an area peripheral to the area of highest color density is located and a second measurement of color density is generated. This peripheral area represents tho background density of the substrate, which can be considered to be the background “noise”. The presence or absence of the analyte in the liquid sample is calculated by adjusting the first measurement with said second measurement in accordance with a predefined mathematical function.

REFERENCE TO RELATED APPLICATIONS

This is a continuation of application Ser. No. 08/465,089 filed Jun. 5,1995. This is a continuation-in-part application of U.S. Ser. No.08/023,113 filed Feb. 26, 1993 now abandoned.

FIELD OF INVENTION

The present invention relates generally to systems and methods ofanalyzing specimens, preferably specimens of biological origin, andparticularly to computerized methods and systems for optical analysis ofsuch specimens.

BACKGROUND OF THE INVENTION

Many laboratory tests are determined by how a particular analyte presentin sample reacts with a specific reagent. Often, these tests arequalitatively determined by visual inspection. For example, current homepregnancy tests can detect human chorionic gonadotropin (HCG), a hormonesecreted in the urine of pregnant women. Typically, the urine is appliedto a testing substrate that has an antibody immobilized thereon that iscapable of binding to the HCG. A labelled reagent is then applied to thetesting substrate that is capable of specifically binding to HCG, andthus, in the presence of HCG, will color the testing substrate, thusindicating a potential pregnancy. For such tests, the user can tell theresults at a glance. However, with increasing demand for rapiddiagnostic testing in a laboratory setting, visual inspection by a humantechnician becomes a bottleneck. In addition, human technicians areerror prone, especially when performing diagnostic tests that requirequantitative measurements of color or optical density. Furthermore,quantifying test results is very difficult for human technicians whenthe color density of the testing substrate varies due to differences inthe amount of reagent used for each test, the amount of liquid (such asblood plasma) deposited on the substrate, or by different batches ofreagents used in the test. Additionally, the results of such tests oftendepend on the difference in color saturation associated with a specificregion of the testing substrate where the analyte specifically bindscompared to another region of the testing substrate where the analyte isnot supposed to bind and thus where the presence of color indicates thedegree of “background” or “noise” in the test. This is particularly truefor rapid immunoassays that use membranes as the testing substrates thathave discrete zones having receptors immobilized thereon thatspecifically bind to the analyte present in the sample tested.

Consequently, a number of prior art systems have been designed topartially automate the process of quantifying test results. For example,the results of electrophoretic immunoblots (Western Blots), the mainmethod for verification of human immunodeficiency virus seropositivity,can be quantitated using densitometry. Typically with a Western Blot,bands of electrophoresed proteins are transferred to a nitrocellulosestrip and then incubated with patient sera. If antibodies specific tothe proteins are present in the sera, they will bind to the blottedproteins. The presence of the antibodies can be detected using labelledantibodies to human IgG. If labels are used that generate a visiblecolor, bands will appear that correspond to the location of the blottedproteins for which the patient has antibodies. The concentration of theantibodies can be quantitated using a densitometer, an instrument whichmeasures optical density by measuring the intensity of reflected light.The nitrocellulose strip is passed through a beam of light, so that theintensity of each band is measured and a value is generated thatcorrelates to the concentration of antibody present in the patient sera.However, the densitometer only measures one point of each band asopposed to scanning the entire area of the band. Because the colorintensity of a band can vary, as well as the background colorsurrounding each band, the values generated by densitometry can vary andthus may not accurately reflect the true concentration of the substancebeing measured.

Reflectormeters are also used to quantitate the results of certainlaboratory tests, particularly, rapid immunoassays such as thosedescribed in U.S. Pat. Nos. 5,006,464 to Chu etal. and 4,632,901 toValkirs et al., which, after the performance of assay steps, can resultin the appearance of a colored region on a testing substrate to indicatethe presence of a particular analyte in a sample. The reflectometer is aphotoelectric instrument for measuring the optical reflectance of asurface. Typically, the rapid immunoassay comprises a testing substratesuch as a porous membrane. A small portion of the testing substrate hasa receptor immobilized thereon (i.e. the receptor area—usually a smallcircular area or dot) that is capable of binding directly or indirectlyto an analyte such as an antibody, protein, hormone, or any othersubstance that is suspected of being present in a patient sample. Thus,when a patient sample, such as plasma or urine, comes in contact withthe testing substrate, the analyte, if present in the sample, will bindspecifically to the receptor area of the testing substrate, but not tothe peripheral area of the testing substrate where no receptor isimmobilized. The remainder of the sample and any unbound analyte willflow through the testing substrate, if it is porous, and/or can bewashed off. A labeled reagent is added that is capable of bindingdirectly or indirectly to the analyte to generate a colored dot orcircle (or whatever shape the receptor area is). Thus, if the analyte ispresent in the patient sample, it will bind to the receptor area and itspresence will be indicated by the generation of color after applicationof the labeled reagent.

The results of the immunoassay can then be measured using areflectometer. Typically, the testing substrate needs to be insertedinto the reflectometer so that the receptor area will align with a beamof light that is used to measure reflectance. Therefore, if the receptorarea is not accurately positioned on the testing substrate, the resultsof the assay will not be accurately measured. Additionally, there may bevariation in the color intensity generated at the receptor area. Thus,the beam of light may not line up with the part of the receptor areathat most accurately correlates to the concentration of analyte presentin the patient sample.

Digital analysis has been used in some testing procedures, but has notbeen used for quantifying the results of immunoassays. For example, U.S.Pat. No. 5,018,209 issued May 21, 1991 and U.S. Pat. No. 5,008,185issued Apr. 16, 1991, both to Bacus, describe digital image processingmethods and apparatus to analyze various features of cells being viewedon a slide under a microscope. Because the cells (or portions thereof)are randomly located on the slide, the technician and system work in aninteractive fashion whereby the technician manually locates the cells onthe slide that the system thereafter analyzes. Thus, while theefficiency of the testing process is increased by such an interactivesystem, it is not as efficient as one which would automatically locatethe region of interest without human interaction.

U.S. Pat. No. 4,922,915 issued May 8, 1990 to Arnold, describes anautomatic image location method in the field of medical imagingtechnology, such as computer tomography (CT) and magnetic resonanceimaging (MRI). In a typical diagnostic scan of a patient, severalreference samples of known optical density are placed in proximity withthe patient's body and are scanned simultaneously. These images of thereference samples of known density are compared with the images ofvarious regions of the patient's body to determine the relevantcharacteristics of those regions.

The method in Arnold is concerned with locating two regions: thereference samples and the regions of interest within the patient's body.With respect to the reference samples, the system locates the samplesautomatically by two separate algorithms. The first algorithm uses thefact that the reference samples are of known optical densities. TheArnold system searches the entire digital image for regions with theseoptical densities.

The second location algorithm uses pre-positioned metallic rodsproximately placed to the reference samples. Initially, the systemstarts scanning the entire digital image for pixels of greatest density.These pixels correspond to the metallic rods. Once the rods are located,the reference samples are easily located because the orientation of thesamples in relation to the metallic rods is predefined.

With respect to locating regions of interest in the patient's body, thesearch performed by the Arnold system is not fully automated. After thereference samples are located, Arnold requires that a human operatordefine an enlarged region of interest, for example around a bonestructure, which the system thereafter refines. This step in Arnold isnecessary because the system is unable to exclude regions which adderror to the density readings.

While Arnold's method of automatically locating digital images workswell when regions are either of known densities or known orientations,it is not satisfactory when the region of interest has neither knownintensity or position. In Arnold's method, human interaction during theanalysis step is always required.

The above-mentioned methods of digital analysis do not preformquantitative analyses of specimens, but rather only locate a region ofinterest based on optical density. However, in the analysis of chemicaland biological specimens, it is often the density of a particular colorthat is the relevant measurement parameter. For instance, someimmunoassays employ labeled reagents, such as certain colloidalreagents, that generate a color when an analyte is detected in abiological specimen.

Therefore, it is an object of the present invention to provide a systemand method for automatic image location and quantitative analysis whenthe region of interest is of neither known intensity or position in theimage.

Another object of the present invention is to provide a reliableautomated method for quantifying the results of an immunoassay whereinthe method provides a more accurate measurement that better correspondsto the true concentration of an analyte in a fluid sample compared withprior art methods that use densitometers and reflectometers.

SUMMARY OF THE INVENTION

In summary, the present invention is a method and system for theautomatic analysis of a testing substrate for an analyte derived from aspecimen, such as a specimen of biological origin, when neither theposition nor the optical density (or color density) of the region of thetesting substrate where the analyte, if present, is precisely known. Theinvention also provides a method for more accurately measuring theconcentration of the analyte in the specimen.

The method comprises the steps of applying a liquid sample suspected ofcontaining an analyte to a testing substrate having an immobilizedthereon, in a limited region of the testing substrate, a receptorcapable of directly or indirectly binding to the analyte. A labeledreagent, capable of binding directly or indirectly to the analyte andgenerating a color signal, is added to the testing substrate. If theanalyte is present, a color is generated at the area of the testingsubstrate where the receptor is immobilized.

The testing substrate is then illuminated and, using electronicequipment, a digital image of the testing substrate is acquired. Inpreferred embodiments, the testing substrate is illuminated usingreflected light. The illumination is pre-calibrated to correct forlighting intensity variations. The digital image is automaticallyscanned to locate an area of the testing substrate having the highestcolor density and generating a first measurement of color density thatcorresponds to pixels per unit area. To aid in the scanning of thedigital image, one embodiment of the invention employs a positionalmarker on the substrate (such as a dark or colored circle, line, spot,or any other shape) to generally indicate where the immobilized receptoris located. The use of a positional marker reduces both the amount oftime require to locate the receptor area and the degree of error inlocating the most optically dense portion of the testing substrate.

Next, an area peripheral to the area of highest color density is locatedand a second measurement of color density is generated that correspondsto pixels per unit area. Because this peripheral area is not proximateto the receptor area where the analyte, if present in the sample,specifically binds, this area represents the background density of thesubstrate, which can be considered to be the background “noise” in themeasurement of the analyte. In a preferred embodiment, the secondmeasurement is generated that corresponds to the pixels per unit area inan annular region that circumscribes the receptor area. The presence orabsence of the analyte in the liquid sample is calculated by adjustingthe first measurement with said second measurement in accordance with apredefined mathematical function.

In some cases, the result of the test will be interpreted as a binary,positive/negative result according to whether the measurement taken isabove or below a given threshold. In other cases, a continuous range ofvalues may be generated from different samples that correspond to theconcentration of the analyte present in each tested sample.

BRIEF DESCRIPTION OF THE DRAWINGS

Additional objects and features of the invention will be more readilyapparent from the following detailed description and appended claimswhen taken in conjunction with the drawings, in which:

FIG. 1 is a block diagram of a system for optically analyzing biologicaland other analytes.

FIG. 2 shows a sample holder with multiple analytes deposited thereon.

FIG. 3 is a conceptual diagram of the method used to locate theoptically densest portion of an analyte deposited on a substrate.

FIG. 4 is a flow chart of the steps of the present invention.

FIG. 5 is a block diagram of an alternate embodiment of a system foranalyzing biological and other analytes.

FIG. 6 shows the linear titration curve obtained using the opticalanalyzer.

FIG. 7 shows relationship between linearity of titration curve andamount of receptor bound to testing substrate.

DESCRIPTION OF THE PREFERRED EMBODIMENT

The method aspect of the invention involves the analysis and measurementof assay results for the determination of the presence or absence of ananalyte in a sample, preferably a sample of biological origin. The typeof assay that is performed prior to the measurement step can be one ofmany assays known in the art as long as the assay employs a testingsubstrate that has a limited area to which the analyte is concentrated,and a peripheral area to which the analyte does not specifically bind.In a preferred embodiment, the assay is an immunoassay for the detectionof an analyte in a biological sample wherein the testing substrate is aliquid-permeable membrane which has a receptor bound on a limited areathereof. The receptor is capable of specifically binding to the analyte.This type of immunoassay is well known by those skilled in the art andis described in further detail in U.S. Pat. No. 5,006,464 to Chu et al.,incorporated herein by reference.

In general, the analyte can be any substance that may be present in aliquid sample that is to be detected by the assay procedure. Inpreferred embodiments, the liquid sample is of biological origin, suchas urine, plasma, serum, whole blood, and the like. The liquid samplemay also comprise a diluent to which the contents of a throat swab,vaginal swab, bacterial culture, or other biological specimen has beenadded. Thus, in a preferred embodiment, the analyte may be a “biologicalanalyte”, that is any substance present in a biological sample that issought to be detected. For example, the analyte may be an antibody to aparticular virus, such as the Human Immunodeficiency Virus (HIV),Rubella, Herpes Simplex Virus I and II (HSV I and HSV II), etc.; abacteria such as Streptococcus pyogenes or Neisseria gonorrhea; ahormone such as human chorionic gonadotropin (HCG) or luteinizinghormone; a protein, or any other detectable substance that may bepresent in a biological sample. Numerous other possible analytes arelisted in U.S. Pat. No. 5,006,464 to Chu et al. Additionally, the assaymay test for the presence of more than one analyte. Thus, the term“analyte” generally refers to one or more a specific type of substancethat is present in a sample. For example, in the case of an assay forthe diagnosis of pregnancy, the analyte is HCG. However, numerous HCGmolecules would be present in the serum or urine sample of the patient.The term “analytes” or “more than one analyte” refers to more than onespecific type of substance in a sample. For example, an assay thatdetects the presence of HSV I and HSV II is an assay that detects thepresence of more than one analyte (i.e two different analytes).

The liquid sample is applied to a testing substrate. Any testingsubstrate can be used as long a receptor that is capable of binding tothe analyte can be immobilized onto the testing substrate. Thus, thetesting substrate can be a porous or a non-porous surface. In apreferred embodiment, the testing substrate is a porous surface such asa fiberglass or nitrocellulose membrane through which the liquid samplecan flow. Typically, the testing substrate is an exposed surface of animmunoassay device such as the device described in U.S. Pat. No.5,006,464 to Chu et al. Other suitable immunoassay devices that employporous testing substrates are well known in the art.

A limited region of the testing substrate has a receptor immobilizedthereon that is capable of directly or indirectly binding to theanalyte. This region, which may take any shape, but which is typically asmall circle or dot, is hereinafter termed the “receptor area”. If asecond analyte is to be tested simultaneously, then there is a secondreceptor area on the substrate that is separate and distinct from thefirst receptor area. By way of example, if the analyte is a humanantibody to HIV, the receptor may be an HIV antigen. The HIV antigen isimmobilized onto a portion of the testing substrate using known methods.If antibody to HIV is present in the liquid sample, it will specificallybind to the HIV antigen. The remainder of the testing substrate will notspecifically bind to the antibody. Thus, after the liquid sample isapplied to the testing substrate, the analyte, if present in the sample,will be concentrated at the receptor area.

A labeled reagent, capable of binding directly or indirectly to theanalyte and generating a color signal, is added to the testingsubstrate. If more than one analyte is being tested simultaneously, morethan one labeled reagent is added to the testing substrate, eithersimultaneously or sequentially. The term “capable of binding directly”,means that the labeled reagents can specifically bind to the respectiveanalytes. For example, if the analyte is a human IgG, the labelledreagent may be labelled antibody to human IgG, or labelled protein A,which binds to the FC fragment of IgG. The term “binding indirectly”means that at least one intermediate reagent is added to the testingsubstrate that is capable of binding to the analyte, and the labeledreagent is capable of binding to the intermediate reagent. For example,if the analyte is human IgG, an intermediate reagent may be a rabbitantibody to human IgG. The labelled reagent may be a goat antibody thatspecifically binds to the rabbit antibody.

The presence of bound analyte is indicated by the presence of color thatis generated by the labeled reagent. The label may be a coloredsubstance itself, such as colloidal gold which, when concentrated at thereceptor area, generates a red color. Alternatively, the label may be anenzyme which, when substrate for the enzyme is added, causes a coloredproduct to be generated. A variety of labels are well known in the art.Techniques are well-known in the art for attaching labels to reagents. Apreferred embodiment of the invention employs a reagent labelled whichcolloidal gold because an enzyme-substrate reaction is not required togenerate color, thus requiring fewer steps in performing the assay, andhigh sensitivity can be achieved using colloidal labels.

In order to measure the results of the assay, the testing substrate isilluminated and, using electronic equipment, a digital image of thetesting substrate is acquired. In preferred embodiments, the testingsubstrate is illuminated using reflected light. The illumination ispre-calibrated to correct for lighting intensity variations. The digitalimage is automatically scanned to locate an area of the testingsubstrate having the highest color density, i.e. the highest number ofpixels per unit area, and generating a first measurement of colordensity. To aid in the scanning of the digital image, one embodiment ofthe invention employs a positional marker on the substrate (such as adark or colored circle, line, spot, or any other shape) to generallyindicate where the immobilized receptor is located. Once the generalregion for the immobilized receptor is identified, the region will beidentified for the area having highest color density. The use of apositional marker reduces both the amount of time require to locate thereceptor area and the degree of error in locating the most opticallydense portion of the testing substrate.

Next, an area peripheral to the area of highest color density is locatedand a second measurement of color density is generated as determined bythe number of pixels per unit area. Because this peripheral area doesnot include any portion of the receptor area (where the analyte, ifpresent in the sample, specifically binds) its measurement representsthe background density of the substrate and thus the “noise” in themeasurement of the analyte. Background color may result fromnon-specific binding of the analyte or labeled reagent to areas of thetesting substrate where there is no receptor bound. If the assay is doneproperly, the background color should be much less than the colorgenerated at the receptor area when analyte is present in the sample.However, in some cases, even when assay procedures are done properly,portions of the peripheral area can be as dark as the area where analytehas bound specifically to receptor. This can sometimes happen if thebiological sample being tested has particulate matter that is trapped bythe membrane and unable to flow through. Samples that have been frozenand thawed often contain particulate matter that can lead to backgroundproblems.

High levels of background can also occur if the substrate is not evenand, as a result, aggregates in the sample pool at a particular regionof the substrate. In prior art immunoassay methods that employrefractometers, a positive sample that produces high background can befalsely diagnosed as negative if the area of high background on thetesting substrate coincides with the point where background reflectanceis measured. Because the present invention uses digital technology todetermine the number of pixels per unit area, a larger area ofbackground can be measured, not just one point as with reflectance, andthus a more accurate reading can be obtained than is possible with priorart technologies. In a preferred embodiment the background density isdetermined by measuring an annular region that surrounds the receptorarea is measured. If there is more than one receptor area, two annularregions, one for each receptor area, would be measured. Alternatively, asingle large background region could be defined for all receptor areas.The preferred approach for background determination may vary dependingupon the size of the receptor areas, the type of sample to be tested andthe nature of the flow of the sample.

After the region of highest color density (first measurement) andbackground density (second measurement) are determined, the presence orabsence of the analyte in the liquid sample is calculated by adjustingthe first measurement with the second measurement in accordance with apredefined mathematical function as exemplified in more detail below. Ifa positional marker is used that is located within the peripheral area,then the second measurement is adjusted so that the color intensity ofthe positional marker is not included as part of the backgroundmeasurement. Because color intensity can sometimes vary depending uponwhether the testing substrate is wet or dry, the first and secondmeasurements can also be adjusted to take into consideration thisfactor. For example, calibration spots on the testing substrate could beused that have a fixed color intensity, independent of the sample beinganalyzed, but dependent on whether the testing substrate is wet or dry.The calibration spot could also serve a dual purpose as a positionalmarker.

The result of the test can be interpreted as a binary, positive/negativeresult according to whether the measurement taken is above or below agiven threshold. In preferred embodiments, the adjusted measurement,which corresponds to an adjusted number of pixels per unit area, will bequantitative, correlating to the concentration of analyte present in thesample. Typically, for quantitative measurements, a standard calibrationcurve of a known sample would be generated and used to determine theconcentration of the sample tested based on the measurements generatedfrom the test sample.

In describing the system aspect of the present invention, reference ismade to FIG. 1, where there is shown a block diagram of the system foroptically analyzing biological and other analytes designed in accordancewith the principles of the present invention. System 100 includes acentral processing unit (CPU) 102, computer memory 104, user interface106, system communication bus 108, and an optical measurement subsystem110. The optical measurement subsystem 110 includes a shadowless (i.e.,uniform) light source 112, camera 114, and camera interface 116. Theoptical measurement subsystem 110 is typically enclosed in a housing 118so that optical images of analytes can be obtained under controlledoptical conditions.

Memory 104, which will typically include both random access memory andsecondary memory such as magnetic disk storage mechanisms, issufficiently large enough to store a plurality of digital images 120,analyte measurement program 122, and a light source calibration program124. Alternatively, programs 122 and 124 could be stored on Read OnlyMemory (ROM) chips.

It should be noted that the specific memory devices used are notimportant to the operation of the present invention so long as they havesufficient capacity and operating speed to enable the optical imageanalysis tasks described below.

The user interface 106 will typically include at least one outputcommunication device such as a printer 125 and/or monitor 126 forcommunicating the results of tests conducted by the system, and at leastone input communication device such as keyboard 127 and/or mouse pointerdevice 128. Many other combinations of user interfaces could be used,and the specific interfaces shown in FIG. 1 should not be construed as alimitation.

Before any testing substrates are analyzed, light source 112 iscalibrated. Calibration is performed each time the system is powered on,and may need to be performed periodically if the system is kept on forlong periods of time, because any changes in the light source'sintensity could affect the result of the test. For example, if themeasurement produced by the test is greater than a certain thresholdvalue, the result of the test may be deemed positive. Otherwise, thetest may be negative. These threshold values, stored as constants (or asa mathematical formula) in the analyte measurement program 112, arebased upon a certain light intensity level. Without proper calibration,the possibility of false test results increases.

In the preferred embodiment, calibration is accomplished by calibrationprogram 124 by measuring the light source's intensity with a lightsensor (see light sensor 186 in FIG. 5). In an alternate embodiment ofthe invention, the calibration program 124 takes as input an image of acalibration substrate. In the preferred embodiment a calibrationsubstrate is a regular testing substrate without any analyte depositedon its surface. The intensity of light is measured according to theaverage density of the image of the calibration substrate. Then, acalibration coefficient is computed by dividing the average imagedensity with a predefined standard value. All subsequent image densityvalues are multiplied by this calibration coefficient.

When system 100 is ready for operation, camera 114 takes an analog imageof at least a portion of the top surface of test carrier 129. The topsurface of carrier 129, as depicted in FIG. 1, includes testingsubstrate 130 on which is deposited a chemically active reagent. Priorto insertion of carrier into the optical measurement subsystem 110, ananalyte 132, typically derived from a biological specimen, is depositedonto the region of the test carrier where substrate 130 is located. Inthe preferred embodiment, the chemical interaction of the analytes 132with the chemically active substrate 130 typically causes the analyte132 to be the optically densest portion of the substrate 130.

FIG. 2 shows a test carrier 129′ with multiple analytes 144 deposited onits substrate 130. Positional marker 146 gives the relative position ofsubstrate 130 on carrier 129′. As previously mentioned, marker 146 maybe any shape or size sufficient to indicate the general position orlocation of the substrate 130 and/or the analyte(s) on the test carrier129′.

The analog image generated by camera 114 is digitized by camerainterface 116 and sent via bus 108 to memory 104 where the digital imageis stored as an array of pixel values. In the presently preferredembodiment, the portion of the test carrier 129 captured by the camera114 is {fraction (5/16)}″×{fraction (5/16)}″ and is represented as a170×170 array of pixel elements. Additionally, the presently preferredembodiment has the capability to process both color and gray scaleimages, with 8-bit pixels (256 gray scale levels) being used for grayscale images and 24-bit pixels (256³ levels) being used for colorimages. It should be appreciated that the image could be formed frommore or less pixel elements and more or less scale image levels to alterthe image resolution and sensitivity. It will also be appreciated thatother data structures for image storage are possible.

Note that for some analyte measurement tests the measured “density” ofthe analyte and background regions of the digital image will be thetotal optical density of a portion of the digital image, while for otheranalyte measurement tests the measured density will be the density of aparticular color. That is, when the digital image is a color image eachpixel will be represented by Red, Green and Blue (RGB) values, and thetest measurements can be based on any one or predefined combination ofthe three RGB color values for the image's pixels. Thus, the term“density” in the discussions below concerns the density of a preselectedoptical characteristic of the digital image which is relevant to themeasurement being performed.

After the digital image has been captured, the image is analyzed byanalyte measurement program 122. This analysis includes locating theanalyte by locating within the digitized image a circular region ofpredefined size having the greatest optical density, locating a“background” region of the substrate 130 that is not covered by theanalyte, and computing a test result by computing a predefinedmathematical function of the average density of the background regionand the average density of analyte region. The mathematical function maybe as simple as subtracting the background density from the analytedensity, or may be a considerable more complex function. In thepreferred embodiment, the circular region of greatest optical density issized to be small enough so as to be entirely covered the smallestanticipated analyte, and thus the average optical density of thecircular region should be representative of the optical density of thechemically reacted analyte.

To accomplish this analysis, analyte measurement program 122 performsthree main processes: pre-scan, fine-scan, and background densitycompensation. It will be appreciated that program 122 executesdifferently according to whether a positional marker is included on thetest carrier 129 or not. Program 122 takes the digital image stored inmemory 104 as input and begins a raster scan of the entire image. If apositional marker is present, program 122 then performs a raster scanacross the image to locate the marker, which will typically be eitherthe pixels of greatest density, or pixels of a particular color. Fromthe orientation of the marker, program 122 will determine a smallerregion of interest. Thereafter, program 122 confines its pre-scan andfine-scan processes to this defined region. If no positional marker ispresent on the substrate, then program 122 executes its pre-scan andfine-scan processes on a predefined region of the digital image.

The pre-scan process searches the region of interest for an area ofgreatest average density. This area will correspond to the reaction ofthe analyte to the reagent. The area should be as large as possiblewhile still fitting entirely within the site of the analyte and shouldbe sufficiently small to avoid noise sensitivity. In the preferredembodiment, the portion of the digital image used to determine theoptical density of the analyte is a circle of diameter 64 pixels across.

FIG. 3 is a conceptual diagram of the pre-scan process used toapproximately locate the densest area of the analyte 132 deposited onthe substrate 130. Please note that FIG. 3 is not drawn to scale, andthat the analyte 132 will typically cover a much smaller fraction of thesubstrate 130 than shown in this conceptual representation of thescanning process. The pre-scan process measures and compares thedensities of a sequence of circular regions 160 arranged in columns androws, where the centers of the columns are spaced apart by a distance ofΔX and the centers of the rows are spaced apart by a distance of ΔY. Bycomparing the densities of these regions the prescan process determinescenter of the circular region 160 of greatest density, as represented bycircular region 162, and thereby locates the approximate center of theanalyte. Table 1 contains a pseudocode representation of this process.

TABLE 1 PRESCAN PROCESS -- Specify range of regions to be tested: X1, Y1= center of top-left region to be tested X2, Y2 = center of bottom-rightregion to be tested -- CX, CY and CD represent the position and density-- of the region of greatest optical density found so far. CX = X1 CY =Y1 CD = 0 For X = X1 to X2, by steps of size ΔX { For Y = Y1 to Y2, bysteps of size ΔY { Measure density D of region centered at X,Y within aradius of Z pixels -- Update center value whenever higher density region-- is found If D > CD { CX = X CY = Y CD = D } } }

After the region of greatest optical density is approximately found, thefine-scan process is used to more precisely locate the reaction regionof greatest optical density. The fine-scan process takes as its inputthe center of the area of greatest density obtained from the prescanprocess. The center of the area is then shifted by one or two pixelelements in both the X and Y coordinates. The densities of theseresulting areas are then calculated by summing the pixel elementreadings for the areas. The measured optical or color density for eacharea is compared with the greatest density located by the pre-scanprocess, and the greatest density area is accordingly updated. Thefine-scan process then computes the average pixel density for the areaby taking the greatest density reading and dividing by the number ofpixels in the circle. This average density is the output result of thefine-scan procedure. Table 2 contains a pseudocode representation ofthis process.

TABLE 2 FINE-SCAN PROCESS -- Initialize the starting X and Y ranges fromthe -- center of the region found in Prescan. X_START = CX Y_START = CY-- Let S1, S2, S3, S4, S5 and S6 be relatively small -- integer valuesgreater than zero. For X = X_START − S1 to X_START + S2, by steps of S3{ For Y = Y_START − S4 to Y_START + S5, by steps of S6 { Measure densityD of region centered at X, Y within a radius of Z pixels. -- Updatecenter value whenever higher -- density region is found. If D > CD { CS= X CY = Y CD = D } } }

After the fine-scan process refines the center coordinates of the regionof greatest density, the analyte measurement program 122 then performs abackground compensation step. To obtain the necessary backgroundreading, annular region 136, as shown in FIG. 1, is selected by program122. Annular region 136 has an inner radius sufficiently large such thatnone of the analyte 132 is found in region 136. An average pixel densityfor annular region 136 is computed as discussed above. The measureddensity of the analyte is then adjusted in accordance with themeasurement background region density. In some cases the adjustment issimply a subtraction operation, while in others it may be accomplishedby division or other mathematical operation.

This adjusted measurement value may be interpreted as the result of thetest according to the nature of the reaction of the analyte with thereagent. In some cases, a simple threshold test will result. That is, ifthe adjusted measurement value is greater than a pre-determinedthreshold, then the test is considered positive. Otherwise, the test isconsidered negative. Alternatively, the adjusted measurement value maybe a value in a continuous range of values that is to be interpreted bythe user, or that is mapped with respect to a predefined scale and thenpresented for interpretation by the user. Thus, the adjusted measurementvalue may correspond to concentration of analyte present in the sample.

The flow chart in FIG. 4 represents the sequence of steps used to testan analyte, from depositing the analyte onto the substrate throughgeneration of the final measurement value.

An alternate embodiment of the present invention is depicted in FIG. 5.Instead of a positional marker being affixed to individual carriers, asshown as marker 146 in FIG. 2, a separate template 180 is positionedbetween camera 114 and carrier 129. The image of template 180 is thussuperimposed upon the image of carrier 129 when the image is captured.To insure the proper alignment of the two images, template 180 wouldremain in a fixed location; while carrier 129 would be slid intoposition by way of guide rails 182. The image of template 180 would beused to mark the region where the analyte is deposited on the substrate.Use of the template would obviate the need to place position markers onindividual carriers.

Also depicted in FIG. 5, a light sensor 186 can be positioned inside themeasurement subsystem's housing 118 to measure the intensity of lightemitted from light source 112. In this embodiment, readings from sensor186 are used to calibrate the light source. This makes the calibrationprocess totally automatic and thus the user is not required to performor assist with the calibration process.

It will be appreciated that, although the presently preferred embodimentis currently used for the detection of antibodies to the humanimmunodeficiency virus (HIV), that application area is one of manypotential applications and should not be construed as a limitation. Infact, the method and system of the present invention is broad enough toinclude the automatic testing of any analyte that visually reacts withany reagent.

It will further be appreciated that the present invention overcomesproblems in prior automated systems. Specifically, the present inventiondoes not require a human operator to work interactively at the analysisphase with the system to indicate the regions of interest for testing.Likewise, the present invention is able to locate the specific regionsof interest without precisely knowing in advance either their locationor their optical densities on the digital image.

EXAMPLE 1 Generation of Standard Curve

The exposed membrane of an immunoassay testing device was pretreatedwith a 1:10 dilution of normal human serum in phosphate buffered salineand dried. Protein A-colloidal gold at concentrations of 14.2 ng/μl,7.12 ng/μl, 3.56 ng/μl and 1.78 ng/μl was inoculated onto the pretreatedmembranes in triplicate (i.e. 3 separate devices for eachconcentration). The digital readings generated by the colloidal gold wasmeasured using the optical analyzer system described herein. The resultswere tabulated and plotted and are shown in FIG. 6. The resultsdemonstrate that the reading obtained from the optical analyzer isconcentration dependent. Thus, a measurement obtained from a samplehaving an unknown concentration of analyte can be compared to this typeof standard curve to generate quantitative results.

EXAMPLE 2 Effect of Concentration of Antigen on Testing Substrate

Recombinant rabbit-anti-HIV recombinant protein antiserum (RbαHIV),having a concentration of approximately 125 μg/ml, was diluted withnormal human serum using 2× serial dilutions. The diluted RbαHIV sampleswere added to the membranes of immunoassay devices having either 0.5 μlor 1.0 μl HIV recombinant antigen inoculated at the receptor area. AProtein A-colloidal gold conjugate was added to each immunoassay device.Measurements were obtained for each dilution of RbαHIV using the opticalanalyzer described herein. The results were tabulated and plotted andare shown in FIG. 7. The results demonstrate that at low concentrationof analyte (RbαHIV) there is not much difference between the low (0.5μl/membrane) and high (1.0 μl/membrane) concentrations of antigen at thereceptor area. However, at higher concentrations of analyte, sensitivityincreases with increased concentration of antigen at the receptor area.Standard curves like this can be prepared so that values from testsamples can be compared with values of samples having knownconcentrations to generate quantitative information about the testsample. Standard curves can also be generated from known samples thathave been assayed and allowed to dry onto the testing substrate prior tomeasurement, thus correcting for variation in measurements that canoccur between wet and dry testing substrates.

While the present invention has been described with reference to a fewspecific embodiments, the description is illustrative of the inventionand is not to be construed as limiting the invention. Variousmodifications may occur to those skilled in the art without departingfrom the true spirit and scope of the invention as defined by theappended claims.

What is claimed is:
 1. A method for determining the presence of at leastone biological analyte in a liquid sample suspected of containing saidone analyte comprising: a) applying said liquid sample to a testingsubstrate having at least one receptor immobilized thereon in at leastone receptor area of said testing substrate, said one receptor beingcapable of directly or indirectly binding to said analyte, said onereceptor area being located in a limited region of said testingsubstrate; b) applying a reagent capable of binding directly orindirectly to said one analyte and capable of generating a color at saidone receptor area when said one analyte is present; c) illuminating saidtesting substrate and acquiring a digital image of said testingsubstrate; d) using data processing equipment, (i) automaticallyscanning said digital image to locate an optically densest portion ofsaid one receptor area and generating a first measurement of the densityof said densest portion; (ii) locating an area peripheral to said onereceptor area and generating a second measurement of density of saidarea peripheral to said one receptor area; and (iii) generating anoutput signal by adjusting said first measurement with said secondmeasurement in accordance with a predefined mathematical function inorder to generate an output signal that indicates whether said oneanalyte is present in said liquid sample.
 2. The method of claim 1wherein said method is also used for the determination of at least asecond analyte, said testing substrate having immobilized thereon in asecond receptor area wherein said second receptor area is capable ofbinding directly or indirectly to a second analyte, said step (d)including locating and measuring the density of first and secondreceptor areas, and generating an output signal for each receptor area.3. The method of claim 1 wherein the adjusted measurement of step(d)(iii) corresponds to the concentration of analyte present in saidsample.
 4. The method of claim 1 wherein said testing substrate is aporous membrane.
 5. The method of claim 1, wherein said substrate isopaque and includes a marker having a predefined spatial relationship tosaid receptor area; said step (d)(i) including locating said marker insaid digital image and then locating said receptor area in said digitalimage based on said markers location.
 6. The method of claim 1, furtherincluding: prior to step (d), measuring optical density of a referencesubstrate and calibrating all subsequent measurements of testingsubstrates in accordance with said reference substrate's measuredoptical density.
 7. The method of claim 1, wherein said digital imagecomprises an N×M array of pixels; said step (d)(i) including: for eachof a selected set of pixel positions spaced apart from each other,measuring the optical density of a region of said digital imageassociated with said each pixel position; and selecting a plurality ofsaid measured regions with highest density, interpolating the pixelpositions associated with said selected measured regions to generate afinal pixel position, and then measuring the optical density of a regionof said digital image associated with said final pixel position togenerate said first measurement.
 8. A method for determining thepresence of an analyte in a liquid sample suspected of containing saidanalyte comprising: a) applying said liquid sample to a testingsubstrate having a receptor immobilized thereon at a receptor area ofsaid testing substrate, said receptor capable of directly or indirectlybinding to said analyte, said receptor area being located in a limitedregion of said testing substrate; b) applying a reagent capable ofbinding directly or indirectly to said analyte and capable of generatinga color at said receptor area when said analyte is present; c)illuminating said testing substrate and acquiring a digital image ofsaid testing substrate; d) using data processing equipment; (i)automatically scanning said digital image to locate a portion of saidreceptor area having greatest density of a predefined color, andgenerating a first measurement of the density of said predefined colorat said located portion; (ii) locating an area peripheral to saidreceptor area and generating a second measurement of the density of saidpredefined color at said area peripheral to said receptor area; and(iii) generating an output signal by adjusting said first measurementwith said second measurement in accordance with a predefinedmathematical function in order to generate an output signal thatindicates whether said analyte is present in said liquid sample.
 9. Themethod of claim 8 wherein said method is for the determination of morethan one analyte, said testing substrate having immobilized thereon morethan one receptor area wherein each receptor area is capable of bindingdirectly or indirectly to a specific analyte, said step (d) includinglocating and measuring the density of said predefined color at eachreceptor area, and generating an output signal for each receptor area.10. The method of claim 8 wherein the adjusted measurement of step(d)(iii) corresponds to the concentration of analyte present in saidsample.
 11. The method of claim 8 wherein said testing substrate is aporous membrane.
 12. A system for analyzing an analyte derived from abiological specimen, wherein said analyte is bound to a receptor area ofsaid substrate wherein a portion of said substrate is not covered bysaid receptor area, comprising: means for acquiring a digital image ofsaid substrate; and data processing means, coupled to said imageacquiring means, for automatically scanning said digital image to locatean optically densest portion digital image depicting said analyte and tolocate a background portion of said digital image not depicting saidanalyte; said data processing means including means for (A) generating afirst measurement of the density of said densest portion, (B) generatinga second measurement of the density of said background portion of saidsubstrate, and (C) generating an output signal by adjusting said firstmeasurement with said second measurement in accordance with a predefinedmathematical function.
 13. The system, as defined in claim 12, furtherincluding: means of illuminating said substrate; and means for sensingthe intensity of said means for illumination; said data processing meansincluding means, coupled to said intensity sensing means, forcalibrating said measurements in accordance with said sensed intensityof said means for illumination.
 14. The system, as defined in claim 12,wherein: a multiplicity of distinct analytes are bound to a multiplicityof distinct receptor areas of said substrate; said data processing meansincluding means for locating an optically densest portion of each saiddistinct analyte, and for generating a first measurement of the densityof said densest portions of each said distinct analyte.
 15. The system,as defined in claim 12, wherein said substrate includes a marker havinga predefined spatial relationship to said analyte; and said dataprocessing means includes means for locating said marker in said digitalimage and for locating said analyte within said digital image based onsaid marker's location.
 16. The system, as defined in claim 12, furtherincluding: a template interposed between said substrate and said meansfor acquiring a digital image, said template forming a superimposedimage on said digitized image of said substrate; a plurality of guiderails sized to receive said substrate so that said image of saidtemplate falls at predefined position with respect to said substrate,thereby indicating where said analyte is deposited on said substrate.